EP1469776A1 - Analyse de l'apnee du sommeil - Google Patents

Analyse de l'apnee du sommeil

Info

Publication number
EP1469776A1
EP1469776A1 EP20030731805 EP03731805A EP1469776A1 EP 1469776 A1 EP1469776 A1 EP 1469776A1 EP 20030731805 EP20030731805 EP 20030731805 EP 03731805 A EP03731805 A EP 03731805A EP 1469776 A1 EP1469776 A1 EP 1469776A1
Authority
EP
European Patent Office
Prior art keywords
phase
effort
phase angle
determining
thoracic
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
EP20030731805
Other languages
German (de)
English (en)
Inventor
Anand Kumar
Winni Hofman
William Burzelewski
Stephen H SHELDON
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Medcare Flaga hf
Original Assignee
Medcare Flaga hf
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Medcare Flaga hf filed Critical Medcare Flaga hf
Publication of EP1469776A1 publication Critical patent/EP1469776A1/fr
Ceased legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6802—Sensor mounted on worn items
    • A61B5/6804—Garments; Clothes
    • A61B5/6805—Vests
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
    • A61B5/113—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb occurring during breathing
    • A61B5/1135—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb occurring during breathing by monitoring thoracic expansion
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/48—Other medical applications
    • A61B5/4806—Sleep evaluation
    • A61B5/4818—Sleep apnoea
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/08—Detecting, measuring or recording devices for evaluating the respiratory organs

Definitions

  • Obstructive Sleep Apnea one of the most common disorders in the U.S.
  • Lower oxygen levels associated with Obstructive Sleep Apnea (OSA) is now known to be a major cause of cardiovascular morbidity including heart attack and stroke.
  • OSA Obstructive Sleep Apnea
  • expensive poiysomnography is used to identify these patients but not on a sufficient scale to provide diagnosis as a practical matter.
  • the development of a diagnostic system which can allow simplified diagnosis of obstructive sleep apnea by the primary care physician would be a major step.
  • the prevention of hundreds of thousands of annual excess deaths, stroke and heart attacks associated with obstructive sleep apnea through simplified recognition of this disorder is the most important purpose of the present invention.
  • Obstructive sleep apnea often develops insidiously as a patient enters middle age and begins to snore.
  • the major cause is an increase in fat deposition (often age related) in the neck which results in narrowing of the airway. (In fact the probability that a 40 year old has sleep apnea is directly related to his or her neck circumference).
  • the muscle tone of the upper airway diminishes during sleep coupled with negative pressure associated with inspiration through this somewhat narrow airway, this can result in collapse of the upper airway in a manner analogous to the collapse of a cellophane straw. This results in airway obstruction and, effectively chokes off all air movement.
  • the choking patient (still asleep) begins to struggle and inhales more forcibly, thereby, further lowering upper airway pressure and causing further collapse of the upper airway.
  • substantially no air movement into the chest occurs and the patient experiences a progressive fall in oxygen (similar to the fall occurring early in drowning).
  • the fall in oxygen produces central nervous system stimulation contributing to hypertension and potential heart and blood vessel injury and finally results in arousal.
  • increase in airway muscle tone opens the airway and the patient rapidly inhales and ventilates quickly to correct the low oxygen levels.
  • the arousal is brief and the patient is not aware of the arousal (or of the choking since this occurs during sleep).
  • each apnea event is quite variable from patient to patient and with the same patient throughout the night. Indeed, the disease process represents a spectrum of severity from mild snoring, which is associated with incomplete and inconsequential airway obstruction, to severe apneas which can result in fatal hypoxemia.
  • This disease commonly results in excessive daytime sleepiness and can disrupt cognitive function during the day due to fragmentation of sleep during the night associated with recurrent arousals of which the patient is not aware.
  • this disease commonly affects obese patients, it may occur in patients with any body habitus. Because this disease is so common and because it presents with the subtle and common symptoms of excessive daytime sleepiness, morning headache, and decreasing ability to concentrate during the day, it is critical that an inexpensive technique for accurately diagnosing and treating this disease be developed.
  • this disease has been diagnosed utilizing a complex and expensive multi-channel polysomnogram. This is generally performed in a sleep laboratory and involves the continuous and simultaneous measurement and recording of an encephalogram, electromyogram, electroculogram, chest wall plethysmogram, electrocardiogram, measurements of nasal and oral air flow, and pulse oximetry. These, and often other, channels are measured simultaneously throughout the night and these complex recordings are then analyzed to determine the presence or absence of sleep apnea.
  • nocturnal oximetry alone has been used as a screening tool to screen patients with symptoms suggestive of sleep apnea to identify whether or not oxygen desaturations of hemoglobin occur.
  • Microprocessors have been used to summarize nocturnal oximetry recordings and to calculate the percentage of time spent below certain values of oxygen saturation
  • oxygen desaturation of hemoglobin can be caused by artifact, hypoventilation, or ventilation perfusion mismatching. For these reasons, such desaturations identified on nocturnal oximetry are not specific for sleep apnea and the diagnosis of sleep apnea has generally required expensive formal poiysomnography.
  • PSG poiysomnography
  • EEG electroencephalograms
  • EOG electrooculograms
  • EMG electromyograms
  • Some of the newer of these portable systems offer comprehensive software for display and analysis of the collected sleep data, and some offer automatic sleep event scoring.
  • scoring has been found to have varying degrees of reliability due to the technical problems associated with assuring good signal fidelity in the monitored parameters.
  • all of these systems recommend for accurate identification of abnormal sleep events that the data be interpreted and evaluated by experienced clinicians or trained PSG technicians. Since PSG scoring is largely subjective, experienced scorers can generally interpret with good accuracy the action and interactions of poorly shaped and time skewed signals. Although these distortions are commonly accepted as normal for manual scoring, such poor fidelity signals would be unsatisfactory for automated or computer-based scoring.
  • All of the current portable sleep testing systems share common, less-than- desirable features for home use: (1) they are bedside portable, but their size and weight does not allow the patient to be ambulatory, which can be essential for diagnosing patients problems such as excessive sleepiness, (2) they are not designed for unattended use - a technician must come to the home for set-up, disconnection and data retrieval, (3) patients must be outfitted with an array of tethered electrode wires and sensors for connection to bulky body monitors or table-top consoles, and (4) most require subjective analysis of the data by highly trained, sleep professionals.
  • the present invention relates to a method of diagnosing sleep apnea that is non-intrusive and quantitative. Diagnosis of sleep apnea can be achieved by monitoring the phase angle between abdominal effort during sleep and thoracic effort during sleep, determining the phase of each effort, determining the difference in phase between each type of effort, and then determining the rate of phase angle change over time. The instability of the phase angle correlates with respiratory distress index (RDI) and thus is a useful tool for diagnosis.
  • RDI respiratory distress index
  • a ventilation support device can dynamically adapt to the respiratory mechanics of a patient, e.g. a COPD patient. This not only speeds up the recovery but also reduces dependence on ventilator.
  • the invention also provides for treatment to detect events and trigger therapy apparatus such as airway positive pressure apparatus whether operating in CPAP (Continuous Positive Airway Pressure), multi-level CPAP, IPAP (Inspiratory Positive
  • BiPAP Bi-level Positive Airway Pressure
  • EPAP Expiratory Positive Airway Pressure
  • Figure 1 is a symbolic representation of abdominal and thoracic effort during breathing and the phase angle between each type of effort and shows how when breathing is "synchronous", “asynchronous” and “paradoxical”.
  • Figure 2 depicts the general process of monitoring and calculating the change of phase angle.
  • Figure 3 shows the data correlation of 49 patients graphing the percentage of time in instable phase angle versus the respiratory distress index of each patient.
  • Figure 4 shows the data correlation of a study 21 children graphing the percentage of time in instable phase angle versus the respiratory distress index of the patient.
  • Figure 5 shows the data correlation of 33 sleeping patients graphing the percentage of time in instable phase angle versus the respiratory distress index of each patient.
  • Figure 6 shows the data correlation of the same 33 sleeping patients (where as periods with wake stages are removed) graphing the percentage of time in instable phase angle versus the respiratory distress index of each patient.
  • Figure 7 shows the phase angle change data generated by a patient displayed in graphic form showing standard deviations from the norm.
  • Figure 8 shows data phase angle change data in graphic form.
  • Figure 9 shows data phase angle change data in graphic form.
  • Fig. 10 illustrates a disposable, wearable garment for diagnosing a patient.
  • the invention recognizes that the phase angle, the difference between the phase of abdominal effort during breathing and thoracic effort during breathing, while useful in diagnosis or screening for respiratory disturbance, is not the most useful factor, but rather the change in phase angle as a function of time is.
  • thoracic and abdominal effort could be measured by mechanical means and graphed on a strip chart as a function of time, the phase of each type of effort could be determined as well as the change of phase, and the instability of the phase angle could be determined. The degree of uncertainty then is used to measure the degree of breathing disturbance the patient demonstrates.
  • the signals are first digitized and data is stored in a computer file.
  • the calculations have no restriction on sample rate. It is however expected that sample rate satisfies the Nyquist rule. For respiration, 10Hz sample rate is nominal value.
  • the computer file reads the signals and performs phase calculation off-line.
  • the method for phase calculation is by cross-correlation between two signals.
  • a sample of the output of that computation is graphically represented in Figure 3.
  • the distance between two adjacent maxima in the cross correlation curve estimates the dominant period time.
  • the distance between zero lag and the nearest maximum is a measure of phase lag. This value is in seconds.
  • Phase in degrees is estimated by the division of estimated phase lag by estimated period time.
  • the user is given the option to sub-sample data at about 10 Hz (any other suitable frequency giving sufficient resolution may be used). This ensures that recordings that have recorded respiratory signals at high sample rates will not result in unacceptable long phase calculation times.
  • the results of the phase calculation are conveniently stored at 1-second intervals (to reduce the storage requirements) .
  • the result is a value per second between -180° and +180° which is indicative for the current phase angle between the two effort signals.
  • the values can be plotted per second in a signal window or as a mean value over a longer period (30 seconds) in an overview window.
  • the standard deviation of the phase angle between the two respiratory signals is calculated over a sample period (generally 30 seconds but this period can be adjusted based upon).
  • standard deviation is used in currently preferred embodiments, other statistical parameters well known in the art of statistical analysis may as well be used to estimate/quantify the changes of the phase angle.
  • Such other statistical parameters include calculation of root mean square successive differences, root mean square error, the interquartile range, percentile range, average absolute deviation from the median, or derived calculations of these including standard error of mean which is derived from the standard deviation.
  • the standard deviation (or other statistical parameter) of the phase angle as well as the original phase values are plotted as a function of time. This gives instantaneous information about the variability of the phase angle over sample period.
  • the changes in phases can also be plotted by calculated difference between adjacent phase values.
  • the variability of the phase angle over a certain period is an indication of the extent to which the phase angle between the two effort signals fluctuates.
  • the standard deviation of the phase angle over a certain period is a statistical method to calculate this variability. Other statistical calculations such as the above mentioned may as well be employed. In one embodiment the standard deviation is presented for every 30 minutes. For diagnostic purposes, shorter period (10 seconds) is chosen to calculate the standard deviation of the phase angle. The following steps are used to calculate this index:
  • phase angle values are made absolute values, so that all negative values are made positive (it does not matter if the phase angle is positive or negative);
  • the method must be chosen based so that variability can be measured.
  • the measure of variability in one case a measure was chosen that for the whole night, the number of 10 second periods with more than 10 standard deviation is summed. This measure was termed a flip-flop state and the percentage of time is calculated. It is called the Flip-Flop State Index.
  • the flip-flop state index is directly related to upper airway obstruction.
  • the Flip-flop state is the unstable state of the respiratory system whereas the interaction between thoracic and abdominal muscles is not synchronized and is unstable.
  • the unsynchronized interaction is calculated by calculating the phase between signals from the effort of abdominal and thoracic muscles.
  • the instability of this synchronization is calculated by calculating fluctuations in phase. If a statistical measure of fluctuations in phase (like standard deviation or other statistical parameter) is above a certain threshold then the respiratory mechanics is in Flip-flop State.
  • the time spent in Flip-flop State during period of measurement is normalized. This normalized time is called Flip-flop State Index. If this index is high, then the particular period of measurement can be labeled to belong to certain disease category.
  • index calculated for sleep is higher than 0.2 (20%), then the patient is expected to have respiratory disturbance during sleep.
  • the index can be used for a more detailed diagnosis, by way of example, if the index is between 20% and 35% then the patient is expected to have upper airway resistance and if it is more than 35% then the patient is expected to have obstructive or central sleep apnea.
  • thoracic abdominal asynchrony is a known measure for has been used for COPD, other respiratory abnormalities and in paradoxical breathing during sleep, it has not been used in diagnosis of apnea.
  • TAA thoracic abdominal asynchrony
  • Literature in this field has been more concerned with the absolute measure of phase angle rather than the rate of phase angle change with time.
  • the rate of change of phase angle correlates to the respiratory disturbance index (the number of times arousal from sleep occurs per hour).
  • a patient is provided with a means for measuring thoracic and abdominal effort.
  • Such equipment might include piezo belts, PDF belts, mercury or pressure strain gauge, pressure sensor, inductance or impedance measurement devices and the like.
  • the design and function of the effort sensors is to allow for monitoring the volume in each region as a function of time and allow determination of the phase of abdominal effort and thoracic effort so that they can be compared and the phase angle difference between the two can be determined.
  • the difference in the phases of the two types of efforts changes over time and is stored for evaluation.
  • a useful embodiment of the apparatus of the invention comprises a wearable garment supporting the means for detecting abdominal effort and thoracic effort is, an example of such apparatus is illustrated in Figure 1 ⁇
  • phase angle instability Besides a manual approach to determining phase angle instability, automated means can be used as well.
  • the abdominal and thoracic phase information could be collected and input into a computer with a software utility that calculates phase change and determines whether there is a significantly significant change or changes in a set of date.
  • this calculation could also be performed by a device with embedded-software on a chip, or analog hardware, or combination thereof.

Abstract

La présente invention concerne un procédé et un dispositif non intrusifs et quantitatifs permettant de diagnostiquer l'apnée du sommeil et de détecter les événements d'apnée par surveillance, pendant le sommeil, de l'effort abdominal et de l'effort thoracique, par détermination de la phase de chaque effort; par détermination de la différence de phase entre chaque type d'effort, et par détermination du rythme de la modification de l'angle de phase et de l'écart type dans le temps. Cette invention concerne également un traitement pouvant être appliqué lors de la détection d'événements d'apnée, lequel traitement consiste à déclencher un dispositif thérapeutique, tel qu'un appareil de pression positive des voies aériennes.
EP20030731805 2002-01-22 2003-01-22 Analyse de l'apnee du sommeil Ceased EP1469776A1 (fr)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
US35077002P 2002-01-22 2002-01-22
US350770P 2002-01-22
PCT/IS2003/000005 WO2003061471A1 (fr) 2002-01-22 2003-01-22 Analyse de l'apnee du sommeil

Publications (1)

Publication Number Publication Date
EP1469776A1 true EP1469776A1 (fr) 2004-10-27

Family

ID=27613426

Family Applications (1)

Application Number Title Priority Date Filing Date
EP20030731805 Ceased EP1469776A1 (fr) 2002-01-22 2003-01-22 Analyse de l'apnee du sommeil

Country Status (3)

Country Link
US (2) US6893405B2 (fr)
EP (1) EP1469776A1 (fr)
WO (1) WO2003061471A1 (fr)

Families Citing this family (48)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7708697B2 (en) 2000-04-20 2010-05-04 Pulmosonix Pty Ltd Method and apparatus for determining conditions of biological tissues
AU5202501A (en) 2000-04-20 2001-11-07 Univ Monash Method and apparatus for determining conditions of biological tissues
EP1549165B8 (fr) 2002-10-01 2010-10-06 Nellcor Puritan Bennett LLC Utilisation d'un bandeau pour indiquer la tension et un système comportant un capteur d'oxygène et un bandeau
US7047056B2 (en) 2003-06-25 2006-05-16 Nellcor Puritan Bennett Incorporated Hat-based oximeter sensor
US7559902B2 (en) * 2003-08-22 2009-07-14 Foster-Miller, Inc. Physiological monitoring garment
DE102004042797B4 (de) 2003-09-03 2022-05-25 ResMed Humidification Technologies GmbH Erfassungsgerät sowie Verfahren zur Observation schlafbezogener Atmungsstörungen
US8412297B2 (en) 2003-10-01 2013-04-02 Covidien Lp Forehead sensor placement
US7878198B2 (en) * 2004-03-31 2011-02-01 Michael Farrell Methods and apparatus for monitoring the cardiovascular condition of patients with sleep disordered breathing
AU2006242838B2 (en) 2005-04-29 2012-02-16 Isonea (Israel) Ltd Cough detector
KR100647905B1 (ko) * 2005-06-03 2006-11-23 한국전자통신연구원 수면 환경 제어 시스템 및 그 방법
AU2007217783A1 (en) 2006-02-16 2007-08-30 Imthera Medical, Inc. An RFID based apparatus, system, and method for therapeutic treatment of a patient
WO2009048581A1 (fr) 2007-10-09 2009-04-16 Imthera Medical, Inc. Système et procédé de stimulation neuronale
US8364220B2 (en) 2008-09-25 2013-01-29 Covidien Lp Medical sensor and technique for using the same
US8257274B2 (en) 2008-09-25 2012-09-04 Nellcor Puritan Bennett Llc Medical sensor and technique for using the same
EP2331201B1 (fr) 2008-10-01 2020-04-29 Inspire Medical Systems, Inc. Systeme de traitement transveineux de l'apnée du sommeil
WO2010042404A1 (fr) 2008-10-09 2010-04-15 Imthera Medical, Inc. Procédé de stimulation d’un nerf grand hypoglosse pour contrôler la position de la langue d’un patient
EP3184045B1 (fr) 2008-11-19 2023-12-06 Inspire Medical Systems, Inc. Système de traitement de troubles respiratoires du sommeil
US8515515B2 (en) 2009-03-25 2013-08-20 Covidien Lp Medical sensor with compressible light barrier and technique for using the same
US9486628B2 (en) 2009-03-31 2016-11-08 Inspire Medical Systems, Inc. Percutaneous access for systems and methods of treating sleep apnea
US8781548B2 (en) 2009-03-31 2014-07-15 Covidien Lp Medical sensor with flexible components and technique for using the same
CA2665651C (fr) * 2009-05-06 2012-06-19 Antna Consulting Corp. Dispositif de detection de la respiration et methode pour detecter la respiration irreguliere ou l'apnee
AU2010318651A1 (en) 2009-11-10 2012-05-03 Imthera Medical, Inc. System for stimulating a hypoglossal nerve for controlling the position of a patient's tongue
US9211085B2 (en) 2010-05-03 2015-12-15 Foster-Miller, Inc. Respiration sensing system
EP2407102A1 (fr) * 2010-07-15 2012-01-18 Tanita Corporation Appareil d'analyse des caractéristiques de respiration et système d'analyse des caractéristiques de respiration
EP2407100A1 (fr) * 2010-07-15 2012-01-18 Tanita Corporation Analyse de caractéristiques de la respiration
US9028404B2 (en) 2010-07-28 2015-05-12 Foster-Miller, Inc. Physiological status monitoring system
US8585606B2 (en) 2010-09-23 2013-11-19 QinetiQ North America, Inc. Physiological status monitoring system
KR20120057295A (ko) * 2010-11-26 2012-06-05 한국전자통신연구원 무구속 착용형 호흡 부전 경보 장치 및 방법
JP6092212B2 (ja) 2011-08-11 2017-03-08 インスパイア・メディカル・システムズ・インコーポレイテッドＩｎｓｐｉｒｅ Ｍｅｄｉｃａｌ Ｓｙｓｔｅｍｓ， Ｉｎｃ． 呼吸努力の検知結果に基づいて刺激プロトコルを選択するためのシステム
WO2013120134A1 (fr) * 2012-02-17 2013-08-22 Visecor Pty Ltd Surveillance respiratoire
EP2953535A4 (fr) 2013-02-09 2017-01-04 Spire Inc. Système et procédé de surveillance de la respiration
EP2978374A2 (fr) * 2013-03-25 2016-02-03 Technion Research & Development Foundation Ltd. Analyseur de l'apnée et de l'hypoventilation
DE112015001216T5 (de) 2014-03-13 2017-01-12 Halare, Inc. Systeme, Verfahren und Vorrichtungen zum Lindern und zur Ergebnisüberwachung von Schlafbezogenen Atmungsstörungen
WO2015138861A1 (fr) * 2014-03-13 2015-09-17 Halare, Inc. Systèmes et procédés de détection et de diagnostic de trouble respiratoire du sommeil
WO2015178439A2 (fr) * 2014-05-20 2015-11-26 株式会社Ａｉｎｙ Dispositif et méthode d'aide au diagnostic de l'apnée centrale/obstructive du sommeil, et support lisible par un ordinateur comportant un programme d'aide au diagnostic de l'apnée centrale/obstructive du sommeil
WO2016011645A1 (fr) * 2014-07-24 2016-01-28 深圳迈瑞生物医疗电子股份有限公司 Procédé et système d'imagerie ultrasonore
EP3881892A1 (fr) 2015-03-19 2021-09-22 Inspire Medical Systems, Inc. Stimulation pour le traitement de troubles respiratoires du sommeil
WO2016156037A1 (fr) * 2015-03-31 2016-10-06 Koninklijke Philips N.V. Appareil de détection d'effort respiratoire porté sur le corps fournissant un démarrage et une initiation de l'enregistrement des données sur un dispositif d'enregistrement de surveillance respiratoire automatiques
WO2018148319A1 (fr) 2017-02-07 2018-08-16 Spire, Inc. Système de surveillance physiologique
EP3638113A4 (fr) 2017-06-16 2021-03-03 Cornell University Procédés et systèmes de détection électromagnétique cohérente en champ proche
US11234640B2 (en) * 2017-06-28 2022-02-01 The Nemours Foundation Non-invasive pulmonary function assessment and treatment of respiratory fatigue
CN107961015A (zh) * 2017-12-30 2018-04-27 湖南明康中锦医疗科技发展有限公司 呼吸障碍检测装置
CA3100324A1 (fr) 2018-05-14 2019-11-21 Cornell University Lecteur rfid collaboratif utilisant un acces multiple par repartition en code (cdma), et procedes associes
US11806127B2 (en) * 2018-06-13 2023-11-07 General Electric Company System and method for apnea detection
AU2020397171A1 (en) * 2019-12-05 2022-07-07 Disati Medical, Inc Systems and methods for determining a degree of respiratory effort exerted by a patient while breathing
WO2021178193A1 (fr) * 2020-03-02 2021-09-10 Makani Science Inc. Combinaison de données provenant de deux capteurs de mesure respiratoire externes en un flux de données
WO2022026623A1 (fr) * 2020-07-29 2022-02-03 Cornell University Systèmes et procédés de surveillance de respiration d'un individu
CN114576840B (zh) * 2021-11-25 2023-06-23 珠海格力电器股份有限公司 基于wifi信道状态检测进行关机的方法、电子设备和介质

Family Cites Families (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB1596298A (en) * 1977-04-07 1981-08-26 Morgan Ltd P K Method of and apparatus for detecting or measuring changes in the cross-sectional area of a non-magnetic object
DE3604986A1 (de) * 1986-02-17 1987-08-20 Hellige Gmbh Einrichtung zur verhinderung von sauerstoffmangelschaeden
US4777962A (en) * 1986-05-09 1988-10-18 Respitrace Corporation Method and apparatus for distinguishing central obstructive and mixed apneas by external monitoring devices which measure rib cage and abdominal compartmental excursions during respiration
US5191893A (en) * 1990-05-18 1993-03-09 Cns, Inc. Volume variation sensor and method for obstructive sleep apnea monitoring
GB9123638D0 (en) * 1991-11-07 1992-01-02 Magill Alan R Apparel & fabric & devices suitable for health monitoring applications
ATE383814T1 (de) * 1997-03-17 2008-02-15 Vivometrics Inc Verfahren zur atmungswellenformanalyse in bezug auf ihren einfluss auf neuromuskuläre atmung
US6306088B1 (en) * 1998-10-03 2001-10-23 Individual Monitoring Systems, Inc. Ambulatory distributed recorders system for diagnosing medical disorders

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See references of WO03061471A1 *

Also Published As

Publication number Publication date
WO2003061471A1 (fr) 2003-07-31
US20030139680A1 (en) 2003-07-24
US6936011B2 (en) 2005-08-30
US20030139691A1 (en) 2003-07-24
US6893405B2 (en) 2005-05-17

Similar Documents

Publication Publication Date Title
US6893405B2 (en) Analysis of Sleep Apnea
US6091973A (en) Monitoring the occurrence of apneic and hypopneic arousals
US9974479B2 (en) Monitoring asthma and other respiratory disorders with calibrated photoplethysmography devices and methods of using the same
KR101309971B1 (ko) 치료 처리중 수면 품질을 유지하고 모니터하기 위한 방법 및 장치
EP2217141B1 (fr) Appareil médical
US11918373B2 (en) Systems and methods for screening, diagnosis and monitoring sleep-disordered breathing
JP5878926B2 (ja) 閉塞性睡眠時無呼吸を診断するための装置及び方法
US7725173B2 (en) Measurement of responsiveness of a subject with lowered level of consciousness
US20070032733A1 (en) Method and apparatus for ECG-derived sleep disordered breathing monitoring, detection and classification
JP2013533021A (ja) 睡眠障害分析のための方法およびシステム
CN111466906A (zh) 穿戴式睡眠监测仪及监测方法
Steltner et al. Diagnosis of sleep apnea by automatic analysis of nasal pressure and forced oscillation impedance
AU743765B2 (en) Monitoring the occurence of apneic and hypopneic arousals
AU3819002A (en) Monitoring the occurence of apneic and hypopneic arousals
Riha Nc4–A1 Nc3–A2

Legal Events

Date Code Title Description
PUAI Public reference made under article 153(3) epc to a published international application that has entered the european phase

Free format text: ORIGINAL CODE: 0009012

17P Request for examination filed

Effective date: 20040819

AK Designated contracting states

Kind code of ref document: A1

Designated state(s): AT BE BG CH CY CZ DE DK EE ES FI FR GB GR HU IE IT LI LU MC NL PT SE SI SK TR

AX Request for extension of the european patent

Extension state: AL LT LV MK RO

17Q First examination report despatched

Effective date: 20071121

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: THE APPLICATION HAS BEEN REFUSED

18R Application refused

Effective date: 20090303